Dynamic bioactive nanofiber scaffolding

ABSTRACT

A resorbable bone graft scaffold material, including a plurality of overlapping and interlocking fibers defining a scaffold structure, plurality of pores distributed throughout the scaffold, and a plurality of glass microspheres distributed throughout the pores. The fibers are characterized by fiber diameters ranging from about 5 nanometers to about 100 micrometers, and the fibers are a bioactive, resorbable material. The fibers generally contribute about 20 to about 40 weight percent of the scaffold material, with the microspheres contributing the balance.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a divisional of co-pending U.S. patent applicationSer. No. 13/721,724, filed on Dec. 20, 2012, which was acontinuation-in-part of co-pending U.S. patent application Ser. No.12/437,531, filed on May 7, 2009, and claims priority thereto.

TECHNICAL FIELD

The present novel technology relates generally to the field of materialsscience, and, more particularly, to a fibrous scaffolding material andsystem for bone graft applications.

BACKGROUND

There has been a continuing need for improved bone graft materials.Although autograft materials, the current gold standard for bone grafts,have the acceptable physical and biological properties and also exhibitappropriate structure, the use of autogenous bone also necessarilyexposes the patient to multiple surgeries, considerable pain, increasedrisk, and morbidity at the donor site. Alternately, allograft devicesmay be used for bone grafts. Allograft devices are processed from donorbone and so also have appropriate structure with the added benefit ofdecreased risk and pain to the patient, but likewise incur the increasedrisk arising from the potential for disease transmission and rejection.Autograft and allograft devices are further restricted in terms ofvariations on shape and size and have sub-optimal strength propertiesthat further degrade after implantation. Further, the quality ofautograft and allograft devices is inherently variable, because suchdevices are made from harvested natural materials. Also, since companiesthat provide allograft implants obtain their supply from donor tissuebanks, supply is uncontrolled since it is limited to the donor pool,which may wax and wane. Likewise, autograft supplies are also limited byhow much bone may be safely extracted from the patient, and this amountmay be severely limited in the case of the seriously ill and weak.

Since 2001, nearly 150 varieties of bone graft materials have beenapproved by the FDA for commercial use. Recently, synthetic materialshave become an increasingly viable alternative to autograft andallograft devices. Synthetic graft materials have the advantages of notnecessitating painful and inherently risky harvesting procedures onpatients, have a minimal associated carry risk of disease transmission,and may be strictly quality controlled. Synthetic graft materials, likeautograft and allograft, serve as osteoconductive scaffolds that promotethe ingrowth of bone. As bone growth is promoted and increases, thegraft material resorbs and is eventually replaced with new bone.

Many synthetic bone grafts include materials that closely mimicmammalian bone, such as compositions containing calcium phosphates.Exemplary calcium phosphate compositions contain type-B carbonatedhydroxyapatite [Ca₅(PO₄)_(3x)(CO₃)_(x)(OH)], which is the principalmineral phase found in the mammalian body. The ultimate composition,crystal size, morphology, and structure of the body portions formed fromthe hydroxyapatite are determined by variations in the protein andorganic content. Calcium phosphate ceramics have been fabricated andimplanted in mammals in various forms including, but not limited to,shaped bodies and cements. Different stoichiometric compositions, suchas hydroxyapatite (HAp), tricalcium phosphate (TCP), tetracalciumphosphate (TTCP), and other calcium phosphate salts and minerals, haveall been employed to match the adaptability, biocompatibility,structure, and strength of natural bone. The role of pore size andporosity in promoting revascularization, healing, and remodeling of bonehas been recognized as an important variable for bone graftingmaterials.

Despite these recent advances, there is a continuing need for syntheticbone graft systems. Although calcium phosphate bone graft materials arewidely accepted, they lack the strength, handling and flexibilitynecessary to be used in a wide array of clinical applications.Heretofore, calcium phosphate bone graft substitutes have been used inpredominantly non-load bearing applications as simple bone void fillersand the like. For more clinically challenging applications that requirethe graft material to take on load, bone reconstruction systems thatpair a bone graft material to traditional rigid fixation systems areused. For instance, a resorbable graft containment system has beendeveloped to reinforce and maintain the relative position of weak bonytissue such as bone graft substitutes or bone fragments from comminutedfractures. The system is a resorbable graft containment system composedof various sized porous sheets and sleeves, non-porous sheets andsleeves, and associated fixation screws and tacks made from polylacticacid (PLA). However, the sheets are limited in that they can only beshaped for the body when heated.

In another example, one known bone graft substitute system incorporatesflat, round, and oval shaped cylinders customized to fit the geometry ofa patient's anatomical defect. This system is used for reinforcement ofweak bony tissue and is made of commercially pure titanium mesh.Although this mesh may be load bearing, it is not made entirely ofresorbable materials, leaving metal mesh residue in the body after thehealing process has run its course.

Thus, there remains a need for resorbable bone grafts with improvedhandling, flexibility, and compression resistance. The present noveltechnology addresses this need.

SUMMARY

The present novel technology relates to a biomaterial scaffolding formedfrom ceramic fibers. One object of the present novel technology is toprovide an improved synthetic scaffolding material for bone growth.Related objects and advantages of the present novel technology will beapparent from the following description.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1. is a first photomicrograph of a dynamic biomaterial scaffoldaccording to a first embodiment of the present novel technology.

FIG. 2. is a second photomicrograph of a dynamic biomaterial scaffoldaccording to a first embodiment of the present novel technology.

FIG. 3. is a third photomicrograph of fibers as found in FIG. 1.

FIG. 4 is a fourth photomicrograph of fibers as found in FIG. 1.

FIG. 5 is a fifth photomicrograph of fibers as found in FIG. 1.

FIG. 6A is a perspective view of a first interlocking, entangledmacroscaffold construct formed of the fibrous biomaterial scaffold ofFIG. 1.

FIG. 6B is a perspective view of a second interlocking, entangledmacroscaffold construct formed of the fibrous biomaterial scaffold ofFIG. 1.

FIG. 6C is a perspective view of a third interlocking, entangledmacroscaffold construct formed of the fibrous biomaterial scaffold ofFIG. 1.

FIG. 7 is a first photomicrograph of a dynamic biomaterial scaffoldincluding glass microspheres according to a second embodiment of thepresent novel technology

FIG. 8 is a second photomicrograph of the embodiment of FIG. 7.

FIG. 9 is a third photomicrograph of the embodiment of FIG. 7.

FIG. 10 is a fourth photomicrograph of the embodiment of FIG. 7.

FIG. 11 is a fifth photomicrograph of the embodiment of FIG. 7.

FIG. 12A is a schematic illustration of a melt-blown process for glassfiber production.

FIG. 12B is a photomicrograph of a melt-blown glass fiber material asproduced by the process of FIG. 12A.

FIG. 12C is an enlarged photomicrograph of the composite of FIG. 12Bshowing a glass sphere enmeshed in glass fibers.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENT

For the purposes of promoting an understanding of the principles of thenovel technology and presenting its currently understood best mode ofoperation, reference will now be made to the embodiments illustrated inthe drawings and specific language will be used to describe the same. Itwill nevertheless be understood that no limitation of the scope of thenovel technology is thereby intended, with such alterations and furthermodifications in the illustrated device and such further applications ofthe principles of the novel technology as illustrated therein beingcontemplated as would normally occur to one skilled in the art to whichthe novel technology relates.

The current use of specific biomaterial scaffolds as mediators in thehealing process of biologic tissues (both hard bone and soft cartilage)has lead to significant increases in the understanding of therequirements and process of healing with synthetic materials. The job ofa scaffold is to provide a three-dimensional framework upon which cellsof the appropriate phenotype (such as osteoblasts for bone andchondrocytes for cartilage) can attach, express relevant signalingmolecules and begin the process of tissue formation. Scaffolds typicallyserve to accommodate the natural healing process by affording theattachment of initial proteins, the release of signals from egressingcells, and/or the creation of the new, de novo, tissue in the structureneeded and dictated by physiologic feedback mechanisms. Themicroenvironment of a scaffold influences its behavior and tissueinteractions from the initiation to the final stages of healing.Complete vascularity, remodeling and ultimate structure of thescaffold-tissue interactions influences the degree of success or failureof the resulting physiologic tissue.

FIGS. 1-5 illustrate a first embodiment bioactive nanofiber scaffold 10according to the present novel technology. The scaffold 10 is made up ofa plurality of partially interlocking and, more typically, interlinkingfibers 15 defining a three-dimensional porous support scaffold or web10. The support web 10 is made up of biomaterial fibers 10 that areinterlinked or interwoven, and some may be fused at their intersections17. At least some of the interlinked fibers 15 may thus move over oneanother with some degree of freedom, yielding a support web 10 that isdynamic in nature. The composition of the fibers 15 used as the struts19 of the resulting dynamic nanoscaffold 10 are typically solid,non-porous pure bioactive glass, ceramic or glass-ceramic formulations,such that within the range of fiber diameter and construct size, thatthe scaffolding fibers 15 are generally characterized as having theattributes of bioactivity. In other words, the glass or like ceramicfibers 15 will react with physiologic fluids in vivo to promote boneapposition and/or tissue apposition, and ultimately, within a reasonabletimeframe after the healing process has run its course, be substantiallyresorbed from the body. These glass/ceramic fibers 15 are typically freeof polymer fillers (especially long-chain polymers) or like materials,as such organic materials are both unnecessary to their production andcannot withstand the formation temperatures experience by the ceramicfibers 15.

The diameters of the fibers 15 defining the dynamic scaffold 10 aretypically sufficiently small to allow for inherent interlinking of theresulting three-dimensional scaffold 10 upon itself, without the needfor sintering, fusing or otherwise attaching the fibers 15 to oneanother at their intersections 17, although some such fusing orattachment may be employed to further stiffen the scaffold 10 ifdesired. Hence the scaffold 10 is self constrained to not completelyfall apart, yet the individual fibers 15 defining the support struts 19are free to move small distances over each other to grant the scaffold10 its dynamic qualities such that it remains flexible while offeringsufficient support for tissue formation and growth thereupon. As will bedescribed in detail below, pluralities of fibers 15 characterized assubstantially having diameters below 1 micrometer (1000 nanometers) aresufficient to form dynamic scaffolding 10, as are pluralities of fibers15 characterized as substantially having diameters below 100 nanometers.The scaffolding 10 may also be constructed from a plurality of fibers 15having multi-modal diameter distributions, wherein combinations ofdiameters may be employed to yield specific combinations of dynamicflexibility, structural support, internal void size, void distribution,compressibility, dissolution and resorption rates, and the like.Typically, the ranges of fiber diameters within a construct typicallyranging from less than about 1 micron (submicron) up to about 100microns; more typically, fiber diameters range from about 0.5 microns toabout 10 microns; still more typically, fiber diameters range from about0.5 to about 6 microns; yet more typically, fiber diameters range from0.5 to about 2 microns; still more typically, fiber diameters range fromabout 1 micron to about 6 microns. In all cases, predetermined amountsof larger fibers may be added to vary one or more of the properties ofthe resultant scaffolding 10 as desired. It should be noted that as theamount of smaller (typically less than 10 micrometer) diameter fibers 15decreases and more of the scaffolding construct 10 contains fibers 15 ofrelatively greater diameters, the entire construct 10 typically tends tobecome less self constrained. Thus, by varying the relative diametersand aspect ratios of constituent fibers 15 the resulting scaffoldstructure 10 may be tailored to have more or less flexibility and lessor more load-bearing rigidity.

One factor influencing the mechanism of a dynamic scaffold 10 is theincorporation of relatively small diameter fibers 15 and the resultingsupport macrostructure 20. Fiber scaffolds 10 may be made by a varietyof methods resulting in an interlinking, partially interlocking,entangled, and/or specifically orientated three-dimensional fiberconstruct 20 (see FIGS. 6A-6C). These fibers 15 are not necessarilycontinuous, but may be short and discrete, or some combination of long,continuous fibers 15 and short, discrete fibers 15. The fibers 15intersect are another way to define intersections 17 and also to definepores or voids 37. The resulting support macrostructure or device 20 maythus be a nonwoven fabric made via a spunlaid or spun blown process, amelt blown process, a wet laid matt or ‘glass tissue’ process, or thelike and may be formed to have the characteristics of a felt, a gauze, acotton ball, cotton candy, or the like. Typically, the fibers 15 areformed from a molten bioactive glass precursor through a melt-blownprocess; more typically, the glass melt precursor is a 45S5 bioactiveglass.

The fibers 15 defining the scaffold construct 20 typically havenon-fused linkages 35 that provide subtle flexibility and movement ofthe scaffolding 10 in response to changes in its environment, such asphysiological fluctuations, cellular pressure differences, hydrodynamicsin a pulsatile healing environment, and the like. This in vivoenvironment can and will change over the course of the healing process,which may last as long as several months or even longer. The scaffold 10typically retains its appropriate supportive characteristics anddistribution of pores 37 throughout the healing process such that thehealing mechanisms are not inhibited. During the healing process, thepores 37 defined by the matrix of interlinking and tangled fibers 15 mayserve to carry biological fluids and bone-building materials to the siteof the new bone growth. The fluids likewise slowly dissolve fibers 15made of bioactive glass and the like, such that the scaffolding 10, andparticularly the pores 37, changes in size and shape in dynamic responseto the healing process.

Scaffolds 10 are typically provided with a sufficiently permeablethree-dimensional microstructure for cells, small molecules, proteins,physiologic fluids, blood, bone marrow, oxygen and the like to flowthroughout the entire volume of the scaffold 10. Additionally, thedynamic nature of the scaffold 10 grants it the ability to detect orrespond to the microenvironment and adjust its structure based on forcesand pressure exerted elements within the microenvironment.

Additionally, scaffolds 10 typically have sufficient three-dimensionalmacrostructure for compliance of the macroscaffold support device 20when physically placed into an irregular shaped defect, such as a void,hole, or tissue plane as are typically found in bone, tissue, or likephysiological site. The device 20 typically experiences some degree ofcompaction upon insertion into the defect, while the permeablecharacteristics of the microstructure are maintained. Typically, as withthe placement of any bone void filler, than the device 20 remains within2 mm of the native tissue in the defect wall.

Physical macroforms or devices 20 made from the scaffolding 10 canappear similar to felts, cotton balls, textile fabrics, gauze and thelike. These forms have the ability to wick, attach and contain fluids,proteins, bone marrow aspirate, cells, as well as to retain theseentities in a significant volume, though not necessarily all inentirety; for example, if compressed, some fluid may be expulsed fromthe structure.

Another advantage of the macroscaffolding devices 20 is their ability tomodify or blend the dynamic fiber scaffolds 10 with a variety ofcarriers or modifiers to improve handling, injectability, placement,minimally invasive injection, site conformity and retention, and thelike while retaining an equivalent of the ‘parent’ microstructure. Suchcarriers ideally modify the macro-scale handling characteristic of thedevice 20 while preserving the micro-scale (typically on the order ofless than 100 micrometers) structure of the scaffolding 10. Thesecarriers resorb rapidly (typically in less than about 2 weeks; moretypically in less than about 2 days) without substantially altering theform, microstructure, chemistry, and/or bioactivity properties of thescaffolding. These carriers include polaxamer, glycerol, alkaline oxidecopolymers, bone marrow aspirate, and the like.

EXAMPLE 1

A tissue growth support device 20 may be constructed from nanofiberscaffolding 10 by spin blowing fibers 15 characterized with diameterstypically less than about 0.1 micrometer into a felt-like fabric. Thefibers are typically randomly orientated to produce a substantiallydensely packed textile and is characterized as having a relatively finepore volume as defined by the interstices or pores 37 between the fibers15. The device 20 typically has the form of a thin, stiff sheet and maybe cut or otherwise shaped as desired.

EXAMPLE 2

A plurality of interlocking fibers 15 are spun or blown into arandomly-oriented assemblage 20 having the general appearance of acotton ball. The fibers 15 are typically characterized as havingdiameters of from less than about 1000 nm (1 micrometer) ranging up toapproximately 10,000 nm (10 micrometers). The resulting cotton-balldevice 20 may be formed with an uncompressed diameter of typically frombetween about 1 and about 6 centimeters, although any convenient sizemay be formed, and may be compressible down to between about ½ and ¼ ofits initial size. The device 20 substantially returns to its originalsize and shape once the compressive forces are removed. By varying therelative diameters of some of the fibers 15, structures ranging from‘cotton ball’ to ‘cotton candy’ may be produced, with varying ranges offiber diameters from less than about 10 nm to greater than about 10microns.

EXAMPLE 3

Fibers 15 may be woven, knitted, or otherwise formed into a fabricdevice 20 having a gauze-like consistency. The fibers 15 are typicallygreater than about one micrometer in diameter and may be as large asabout 100 micrometers in diameter. The micro-scale orientation of thefibers 15 is typically random, although the fibers may be somewhat orcompletely ordered. On a macro-scale, the fibers 15 are typically moreordered. The constituency of these devices 20 may have varying amountsof smaller fibers 15 incorporated therein to maintain the selfconstrained effect.

FIGS. 7-11 illustrate another embodiment of the present noveltechnology, a bioactive nanofiber scaffold 110 as described above withrespect to FIGS. 1-6, but having ceramic or, more typically, glassmicrospheres, beads or shot 140 distributed therethrough. The glass shot140 is typically made of the same general bioactive composition as thefibers 115, but may alternately be made of other, different bioactivecompositions. The glass shot 140 is typically generally spherical, butmay have other regular or irregular shapes. The glass shot 140 typicallyvaries in size, having diameters ranging from roughly about the width ofthe fibers 115 (more typically, the struts 119) to diameters orders ofmagnitude greater than the typical fiber widths. While smaller shot maytend to lodge in or around fiber intersections 117, larger shot tend tobecome embedded in the scaffolding device 120 itself and held in placeby webs of fibers 115. Pore-sized microspheres may tend to lodge inpores 137. One function of shot 140 is to preserve pore structure anddistribution upon in vivo insertion and compaction of scaffolding device120. Spheres 140 also function to interact with nanofiber matrix 110 toallow scaffolding 120 to be formed into and hold a new shape; in otherwords, interactions of fibers 115 and spheres 140 give rise toshapeability of scaffolding device 120.

The glass shot 140 may be composed of a predetermined bioactive materialand tailored to dissolve over a predetermined period of time when thescaffolding 110 is placed in vitro, so as to release a predeterminedselection of minerals, bone growth media, and the like at apredetermined rate. Likewise, the glass shot 140 may be hollow bioactiveglass, polymer or the like microspheres defining inner core volumesrespectively filled with specific mixture of medicines, nutritivesupplements, antibiotics, antivirals, vitamins, mixtures thereof, or thelike to be released at and around the bone regrowth site at apredetermined rate and for a predetermined length of time. The releaserate and duration of release may be functions of shot size and wallthickness as well as the distribution function of the same.

FIG. 12 details the melt blown process as typically used to produce thescaffold device 120. A melt 200 of bioactive glass is prepared, eitherfrom a batch, from melting already prepared bioactive glass frit, or acombination of the two. Air attenuation 215 is used to impact anddisrupt a stream 220 of melt derived bioactive glass to yield acomposite mixture 110 of glass beads 140 and glass fibers 115. The glassmelt 200 is bottom drained from a melter and compressed air 215 isdirected, typically perpendicular, to the stream 220 in the direction ofa collection area 225, typically a steel tube or the like. Fibers 115and beads 140 are generated simultaneously during air attenuation 215,so the bulk composite material 20 is a collection of fibers 115 andbeads 140 that impacted one another during the process in a molten stateand formed a three dimensional glass composite 110.

The beads 140 typically have a greater mass than the fibers 115, and soretain heat longer, solidify later, and therefore tend to flow aroundand/or bond to multiple fibers 115 during the melt blown process.Typically, the beads 140 become an integral part of the composite 110and do not simply fall out when the device 120 is handled. The multiplefusion points 230 between the fibers 115 and the beads 140 increase theoverall strength of the material 110 and even when compressed orhandled, the beads 140 typically stay embedded in the fiber matrix 110,yielding an advantage over simply adding individual glass beads 140 to abundle of fibers 15 because the materials 140, 15 are not bondedtogether. Even electrospun fibers 15 that may form some beads 140 duringthe electrospinning process do not form multiple bonds during thedrying/curing processes and do not exhibit the advantages of thecomposite 110. If a bundle of fibers 15 and loose beads 140 were to beheated high enough to viscously flow the glass and bond the fibers 15and beads 140, the fibers 15 would likewise bond to each other alongwith the beads 140 and the resulting composite would thus be rigid andinflexible. In contrast, the instant composite material 110 has beads140 that are bonded to multiple fibers 115, while the fibers 115themselves are generally not bonded to each other. This allows thefibers 115 to move relatively freely over one another, at least forshort distances, affording the material 110 flexibility but also keepingthe beads 140 dispersed and intact inside the composite 110.

The air attenuation process 215 allows for tailoring the composite 110makeup by varying the relative bead 140 and fiber 115 content, the bead140 and fiber 115 size distributions, the bulk density of the composite110, and the dissolution rate of the final composite 110. This is doneby controlling the parameters of the process such as the melttemperature, the molten stream diameter, air stream pressure, distancefrom the air nozzle to the glass stream, the shape of the air (i.e.,flat vs. round), the distance from the air attenuation in which thecomposite is collected, and the like. These parameters allow forsignificant control and modification of the properties of the composite110 and can yield a variety of different types of materials.

Movement of the fibers 115 is desired for the fibers 115 to be able toact as a carrier for the glass beads 140, since the fibers 115 typicallymake up, at most, 40 weight percent of the composite 110, typicallycontributing 20 weight percent or less in some applications. Such agreat quantity of beads (i.e., typically more than about 60 weightpercent, more typically, more than about 80 weight percent) cannot becontained by fibers 115 if they are not at least partially bondedtogether. The ability for the composite 110 to be molded and/orcompressed without degrading the composite 110 (such as breaking loosethe beads 140 from the fiber matrix 110) lends versatility to theapplication the composite 110 may enjoy.

For applications of wound or burn care, a composite device 120 of 60weight percent beads 140 and 40 weight percent fiber 115 with a bulkdensity of >0.1 g/cc is desirable for some glass compositions, while acomposite of about 90 weight percent beads 140 and about 10 weightpercent fibers 115 is optimal for other glass compositions, with a bulkdensity of about 0.5 g/cc. This variance arises because bioactive glassdissolution rates are tailorable, so depending on the time a dressing isdesired to be in contact with a wound, the glass composition andcomposite 120 composition can vary. For typical wound care, a glasscomposition that dissolves in a matter of days is advantageous becauseit corresponds with normal managed wound care (2 to 3 times weekly).Other wound applications, especially military may require the dressingto be more chemically durable in an urban environment, and especially ifthe dressing is being used for hemostasis or blood loss control.

Orthopedic implants have both different duties and different requisiteproperties than soft tissue dressings, and require different compositeproperties because they are placed in the bone defect prior to closureof the wound, so a composite device 120 made up of about 80 weightpercent beads 140 and about 20 weight percent fiber 115 with a bulkdensity of >1.0 g/cc is more appropriate. From these examples, oneskilled in the art would appreciate the need for a material to have theability to be compressed over a wide range of bulk densities whileretaining the components of the composite. Glass is often thought of asa rigid and fragile material, and this composite 110 is distinctlydifferent from the known art insofar as it allows significantcompression and flexibility while not damaging the material as a whole.Achieving this sort of a flexible and tailorable composite 110 with afamily of melt derived bioactive glass materials that are proveneffective for healing hard and soft tissue is novel.

A typical device 120 will typically include between about 60 and about95 weight percent beads 140. The beads will typically be present in atypically bell-curve distribution ranging between 30 microns to 3 mm,with 50 weight percent under 500 microns and 90 weight percent under 1.4mm. The bulk density (usable/effective) is typically about 0.1 to about0.5 g/cc for soft tissue applications and between about 0.8 g/cc toabout 1.5 g/cc, more typically from about 1 g/cc to about 1.4 g/cc, andeven more typically between about 1.1 g/cc to about 1.3 g/cc for boneapplications. A typical graft size range is from about 0.5 cc to about20 cc, more typically between about 3 cc and about 10 cc for bone. Asoft tissue dressing typically varies in size from about 0.1 cc to about300 cc or more, depending on the application. The degradation rate fororthopedic applications is typically, by weight, may be expressed as amaximum of 70% unreacted graft after 4 weeks, 50% unreacted graft in 8weeks, and 20% unreacted graft after 12 weeks in a bone void with <5%graft remaining after 24 weeks. The fiber carrier is typically greaterthan 90 percent reacted in 1 to 4 weeks, more typically in 2 to 3 weeks.

EXAMPLE

A scaffold device 120 composed of melt derived bioactive glass beads 140with a generally randomly interwoven, interlinked, and physically bondedfiber carrier matrix 115 of generally the same composition. The fibers115 are typically substantially between 1 micron and 30 microns indiameter, and are between about 5 weight percent and about 30 weightpercent of the device 120. The glass beads 140 typically connect to thefibers 115 in multiple locations, with a plurality of fibers 115typically connecting to each bead 140. The scaffold device 120 istypically pliable, flexible, and formable, especially after being wettedby blood, bone marrow aspirate, or other bodily fluids. Multiple fibers115 are bonded to the glass beads 140, hence making the composite 140more durable and resistant to breaking due to forming and compression.

In some embodiments, the fibers 115 may be crystallized or partiallycrystallized.

While the novel technology has been illustrated and described in detailin the drawings and foregoing description, the same is to be consideredas illustrative and not restrictive in character. It is understood thatthe embodiments have been shown and described in the foregoingspecification in satisfaction of the best mode and enablementrequirements. It is understood that one of ordinary skill in the artcould readily make a nigh-infinite number of insubstantial changes andmodifications to the above-described embodiments and that it would beimpractical to attempt to describe all such embodiment variations in thepresent specification. Accordingly, it is understood that all changesand modifications that come within the spirit of the novel technologyare desired to be protected.

1-11. (canceled)
 12. A method for producing a resorbable, flexible bone graft scaffold material comprising: forming a plurality of resorbable fibers; interlinking the plurality resorbable fibers to define a fabric having a plurality of open pores; and filling at least some of the open pores with bioactive, resorbable ceramic microspheres; wherein the fibers are characterized by fiber diameters substantially ranging from about 5 nanometers to about 10 micrometers; and wherein the microspheres are characterized by diameters ranging up to about 3 millimeters.
 13. The method of claim 12 and further comprising: inserting the fabric into a void into which bone is desired to grow.
 14. The method of claim 12 wherein the fibers and spheres are respectively composed of a material selected from the group including calcium phosphate, hydroxyapatite, bioactive glass and combinations thereof.
 15. The method of claim 12 wherein the fibers are substantially composed of 45S5 bioactive glass.
 16. The method of claim 12 wherein the fabric further comprises at least one rapidly resorbing carrier material.
 17. The method of claim 16 wherein the rapidly resorbing carrier material is selected from the group including polaxamer, glycerol, alkaline oxide copolymers, bone marrow aspirate, and combinations thereof.
 18. The method of claim 12 wherein at least some of the fibers are fused together at their intersections.
 19. The method of claim 12 wherein the pores carry biological material in communication with new bone.
 20. The method of claim 12 wherein the glass microspheres define hollow shells and wherein the glass microspheres are filled with medicine.
 21. The method of claim 12 wherein the microspheres contribute from about 60 weight percent to about 80 weight percent of the scaffold material.
 22. A method for regenerating tissue, with a resorbable, flexible bone graft scaffold material comprising: interconnecting a plurality resorbable fibers to define a flexible scaffolding material having a plurality of open pores; and filling at least some of the open pores with bioactive, resorbable ceramic microspheres to define a tissue regrowth scaffolding material; filing a wound with tissue regrowth scaffolding material; wherein the interconnected fibers are able to move relative to one another; wherein the respective fibers have respective fiber diameters between about 5 nanometers and about 10 micrometers; and wherein the microspheres have respective sphere diameters from about 1 nanometer to about 3 millimeters.
 23. A method making and using a resorbable, flexible bone graft scaffold material comprising: forming a plurality of resorbable fibers; interlinking the plurality resorbable fibers to define a fabric having a plurality of open pores; and filling at least some of the open pores with bioactive, resorbable ceramic microspheres; interconnecting a plurality resorbable fibers to define a flexible scaffolding material having a plurality of open pores; and filling at least some of the open pores with bioactive, resorbable ceramic microspheres to define a tissue regrowth scaffolding material; filing a wound with tissue regrowth scaffolding material; wherein the fibers are characterized by fiber diameters substantially ranging from about 5 nanometers to about 10 micrometers; wherein the microspheres are characterized by diameters ranging up to about 3 millimeters; and wherein the interconnected fibers are able to move relative to one another. 